|Publication number||US7867271 B2|
|Application number||US 10/720,032|
|Publication date||11 Jan 2011|
|Filing date||20 Nov 2003|
|Priority date||20 Nov 2003|
|Also published as||CA2548280A1, CA2548280C, CN1897892A, EP1689323A2, EP1689323B1, US20050113902, WO2005055881A2, WO2005055881A3|
|Publication number||10720032, 720032, US 7867271 B2, US 7867271B2, US-B2-7867271, US7867271 B2, US7867271B2|
|Inventors||Timothy A. Geiser, Charles R. Peterson, Andy Denison, Stephanie Klocke, Samir Patel, Joanna Lubas, Joanne Lumauig, Kathy Lind, Keif Fitzgerald|
|Original Assignee||Advanced Cardiovascular Systems, Inc.|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (66), Referenced by (12), Classifications (10), Legal Events (2)|
|External Links: USPTO, USPTO Assignment, Espacenet|
The invention relates to stent delivery systems, which are used to implant a stent into a patient's body lumen to maintain the patency thereof. The stent delivery system is useful in the treatment and repair of body lumens, including coronary arteries, renal arteries, carotid arteries, and other body lumens.
Stents are generally cylindrically-shaped devices which function to hold open and sometimes expand a segment of a blood vessel or other body lumen. They are particularly suitable for use to support and hold back a dissected arterial lining which can occlude the fluid passageway therethrough. Stents also are useful in maintaining the patency of a body lumen, such as a coronary artery, after a percutaneous transluminal coronary angioplasty (PTCA) procedure or an atherectomy procedure to open a stenosed area of the artery.
Typically, a stent is delivered intraluminally through a percutaneous incision through the femoral or renal arteries. The stent is mounted on the distal end of an elongated catheter and the catheter and stent are advanced intraluminally to the site where the stent is to be implanted. A variety of devices are known in the art for use as stents and have included coiled wires in a variety of patterns that are expanded after being placed intraluminally. Three different approaches for expanding stents have been developed in the art, namely, balloon expanded stents, elastically self-expanding stents, and heat expanded stents. Balloon expanded stents are placed over a deflated balloon mounted on the catheter. The balloon is then inflated to expand the stent radially outwardly into contact with the arterial wall, whereupon the stent undergoes plastic deformation and remains in an expanded state to hold open and support the artery. Elastically self-expanding stents are adapted to be delivered in an elastically compressed state while confined within an outer restraining sheath, but to elastically expand when the sheath is removed and to provide support to the vessel within which it is implanted. Heat expanded stents are made from heat-sensitive materials such as nickel-titanium, are cooled in a compressed shape before insertion into the patient, but assume a pre-existing expanded shape when exposed to the body temperature of a patient.
With respect to self-expanding stents, typically a retractable sheath is positioned over the self-expanding stent which is mounted on the distal end of the catheter. Once the catheter has been advanced intraluminally to the site where the stent is to be implanted, the sheath is withdrawn thereby allowing the self-expanding stent to expand radially outwardly into contact with the arterial wall, thereby holding open and supporting the artery. Both balloon expanded stents and heat sensitive self-expanding stents may also be delivered within a retractable sheath, similar to that used with a self-expanding stent. In such cases the sheath may function to secure the stent on the catheter during insertion or to prevent sharp edges of the stent from tearing at the wall of the lumen during insertion.
One embodiment of a catheter delivery system is the so-called “over-the-wire” delivery system, in which a catheter is introduced into the patient over a guide wire which has been previously introduced. In this embodiment, the guide wire runs within a lumen extending the entire length of the catheter. Another embodiment of the catheter delivery system is the so-called “rapid-exchange” delivery system, in which the guide wire runs within a lumen in the catheter extending from the distal tip of the catheter to a point just proximal of where the stent is positioned on the catheter, at which point the lumen terminates on the outside of the catheter and the guide wire emerges from the catheter to extend proximally, outside of the catheter. Thus, the catheter of a “rapid-exchange” delivery system has a guide wire lumen port at the distal end of the catheter, and a proximal port spaced a relatively short distance from the distal end and a relatively long distance from the proximal end of the catheter. This “rapid-exchange” configuration allows the surgeon to rapidly and single-handedly place the delivery system over the guide wire or to exchange one delivery system for another, because the length of the guide wire lumen in the catheter is much shorter than that used in an over-the-wire delivery system.
One of the problems associated with the prior art catheter-delivery systems which use a retractable outer sheath is that the addition of a retractable sheath tends to reduce the overall flexibility of the delivery system. However, there is still a need to maintain a low-profile in the distal region of the catheter delivery system in order to track the sometimes tortuous anatomy to deliver the stent to the target area. In this regard, catheter delivery systems still need to utilize a catheter, upon which the self-expanding stent is mounted, that provide a rigid column to allow the physician to push the entire catheter over the pre-deployed guide wire to reach the target area. This stent-mounted catheter also must have sufficient strength to prevent compression or tensile forces from acting on the catheter as it is being delivered over the guide wire. In this regard, the stent-mounted catheter must be able to slide forward and backwards without tangling, kinking or adversely affecting the deployment of the stent.
Another problem that exists in the case of the rapid-exchange delivery system is that the addition of a retractable sheath to surround the catheter introduces a problem of rotational alignment between the sheath and the catheter. Upon commencement of installing the delivery system over the guide wire, the surgeon must introduce the proximal tip of the guide wire into the catheter lumen at the distal tip of the catheter. The surgeon then advances the guide wire proximally through the catheter lumen until the proximal tip of the guide wire emerges from the catheter and protrudes through an opening in the wall of the sheath. If, during the foregoing process, the sheath rotates relative to the catheter, the surgeon may have difficulty in aligning the opening with the guide wire tip, so as to get the guide wire tip to protrude from the opening. This complication can be a major problem for the surgeon to resolve under the pressure of surgery.
Thus, there has been found a need for a reliable rapid-exchange stent delivery system for a self-expanding stent, in which the stent-mounted catheter maintains a low-profile, yet is able to move axially along the deployed guide wire without tangling, kinking or adversely affecting the deployment of the stent. Moreover, there is a need for a reliable rapid-exchange stent delivery system in which rotational alignment between the outer sheath and the catheter may be maintained prior to, and during, the process of positioning the delivery system over the guide wire. Further, the art has found a need for a delivery system for a self-expanding stent which has improved flexibility characteristics. The present invention addresses these and other needs.
The present invention is directed to a catheter delivery system having improved flexibility characteristics. In one aspect, the invention is directed to a rapid-exchange catheter delivery system having an outer member including a restraining sheath portion, in which the sheath is held in rotational alignment with the catheter prior to and during the process of positioning the delivery system over a guide wire. Means for maintaining such rotational alignment may assume the form of a U-shaped member or a tab-like member formed on the outer member of the catheter assembly and adapted to protrude through a slot or opening defined in the stent-mounted portion of the catheter.
A catheter assembly for removably attaching an intravascular stent is provided in which an elongated catheter includes an inner member and an outer member extending along a longitudinal axis, wherein the inner member and the outer member are dimensioned for relative axial movement. A self-expanding stent, having an open lattice structure, and being adapted to be expandable to an open configuration, is mounted on the inner member and restrained by the outer member.
In one particular aspect of the present invention, the inner member of the composite rapid-exchange catheter assembly includes a proximal portion made from a hypotube which minimizes the chance of compression or tensile forces acting on the catheter assembly. The hypotube also provides a channel for flushing the system with a fluid, such as saline, prior to usage. In this manner, the inner member provides a conduit for helping evacuate air bubbles from the catheter assembly prior to usage. In one particular embodiment of the invention, the proximal portion of the inner member can be made from polymeric coated coil tubing which is utilized to help prevent compression of the inner member without decreasing the flexibility of the rapid-exchange delivery system. Such a tubing also could be used in an over-the-wire stent delivery system. In yet another aspect of the invention, the polymeric coated coil tubing could be utilized as the guide wire receiving member for a rapid-exchange version of the self-expanding stent system. The use of this polymeric coated coil tubing should not reduce the flexibility or trackability of the catheter during usage, but should prevent compression or kinking when being deployed.
The present invention includes an anti-rotation member formed on the outer member which is adjacent to the guide wire exit opening. In one particular form of the invention, the anti-rotation member takes on a U-shape or, alternatively, a tab-like member formed on the outer member which engages a similarly shaped lumen formed on the inner member so as to maintain the inner member and the outer member in rotational alignment. It should be appreciated that the shape in which the anti-rotation member is formed can be any one of a number of geometric shapes, including a square, V-shape, and the like. Accordingly, the lumen formed on the inner member would be similarly shaped to fit within the particular shape of the anti-rotation member. The anti-rotation member is adapted to extend radially inwardly and to engage the particular shaped slot in the inner member to allow the inner member and outer member to move axially relative to each other while preventing rotational motion between these components. A guide wire notch and exit opening extend through a slot in the outer member and through the slot in the inner member to create a rapid-exchange system. Axial motion between the inner member and outer member does not interfere with the positioning of the guide wire within the guide wire notch.
In another aspect of the present invention, the distal portion of the outer member which forms the restraining sheath portion of the self-expanding stent delivery system can be made from a Nylon-coated polyimide material that provides high-strength tubing with a low-wall thickness. Such a material can resist an equal amount of hoop stress at a much lower wall thickness than with a Nylon material alone. In one component, a Nylon material is bonded to the outside of a polyimide tubing. The inner surface of the polyimide tubing remains resistant to stent-strut indentation caused by the outward radial force exerted by the collapsed self-expanding stent. The Nylon material bonded to the outside of the sheath portion provides the necessary tubing strength to restrain the stent in a collapsed delivery position, but with a lower wall thickness. As a result, the profile of the stent delivery system can be reduced at its distal region by utilizing such a composite material.
Other features and advantages of the present invention will become more apparent from the following detailed description of the invention, when taken in conjunction with the accompanying exemplary drawings.
The present invention relates to rapid-exchange delivery catheter systems in which a stent is delivered intraluminally into a human patient's body lumen, such as a coronary artery, carotid artery, renal artery, peripheral artery and veins, and the like, and implanted therein.
There are numerous prior art stent delivery systems which may be used in conjunction with the present invention. The stent delivery systems suitable for use with the present invention are “rapid-exchange” delivery systems which have an outer sheath adapted to slide over an inner catheter so as to cover a stent. The invention described in detail herein is described in the context of an elastically self-expanding stent delivery system. However, the invention is not limited to such use, and may equally be used with a delivery system for a balloon expanded stent or heat-expanded stent.
In one embodiment of the invention, as exemplified in
Referring specifically now to
The inner member 24 also includes a guide wire receiving member 42 which defines a lumen and is configured to extend from a proximal end 44 to a distal end 46 located in the region of the distal portion 36 of the inner member 24. The profile of this guide wire receiving member 42 extends distally along and adjacent to the catheter and then deflects from being adjacent to the catheter so that it extends coaxially therewith. The guide wire receiving member 42 terminates in a distal opening 48 at its distal end 46. As is shown in
The inner member 24 further includes a substantially long proximal portion 52 made from a tubular member which is attached to the guide wire receiving member 42 and extends to the proximal end 30. This particular proximal portion can be a support hypotube made from, for example, stainless steel or nickel-titanium alloy, which provides support for the rapid-exchange catheter assembly 20 as well as providing compression and kink resistance to the overall catheter assembly 20. The proximal portion 52 creates a passage to allow a flushing fluid to be introduced into the catheter assembly in order to flush the catheter of unwanted air bubbles. A syringe or similar fluid introducing device can be attached to the luer fitting located on the control handle 28 which allows the flushing fluid to be introduced into the catheter assembly to flush air bubbles from the system. This proximal portion 52 provides a semi-rigid tubular column which creates a reduced profile to allow the composite catheter assembly 20 to reach smaller diameter locations in the patient's vasculature while minimizing the chance for compressive or tensile failures during deployment. As can be seen best in
Referring still to
Referring still to
The outer member 26 further includes an intermediate portion 72 which extends from a proximal end 74 where it is bonded utilizing laser, heat or adhesive to the distal end 68 of the proximal outer member 64. In this regard, the intermediate portion 72 has a larger diameter than the much smaller diameter tapered region formed at the distal most end of the proximal outer member 64. This intermediate portion 72 can be made from a strong but flexible material, such as Nylon 12, and extends distally and is attached to the distal restraining sheath portion 62 which is adapted to extend over the compressed stent 22 to maintain it in a collapsed position until the stent is ready to be deployed. As can be best seen in
As can be best seen in
Referring now to
The outer member 88 of the rapid-exchange catheter assembly 80 is made up of several portions or sections which provide different functions. As is shown in
Referring initially to the proximal portion 100 of the outer member 88, the material and shape of the component forming this section of the outer member 88 can be made from a single lumen tubing, using catheter material well known in the art. The intermediate portion 108 is made from a tubular member having a pair of lumens extending therethrough. In the embodiment of
The guide wire notch 120 (
Referring now to
The use of a coil tubing to form the guide wire receiving member helps to prevent compressibility of the inner member without decreasing the flexibility of the catheter assembly. Thus, in use, the guide wire receiving member will support the direct amount of compression force that is placed on the inner member during deployment, preventing the inner member from compressing and providing accurate stent placement. Such a guide wire receiving member is valuable in situations in which high deployment forces can be developed during deployment. In other words, the higher the deployment force, the more the inner member will compress during deployment. As the diameters of the self-expanding stents increase, along with increased radial strength, a guide wire receiving member which utilizes a coil tubing should help to provide accurate stent placement and absorb the compression exerted on the assembly. Such a guide wire receiving member would still provide increased flexibility and trackability at the distal portion of the catheter assembly as it is delivered through tortuous anatomy.
In the particular embodiment shown in
Referring now to
Referring now to
Referring now specifically to
Generally, the guide wire exit opening 184 is formed on the outer member by piercing the tubular material forming the outer member with a mandrel for initially forming the guide wire exit opening. In this regard, a guide wire which is larger than the diameter of the guide wire utilized with the rapid-exchange catheter assembly is used to create a notch within the outer member. The mandrel can be heated and pressed down onto the outer member to form the U-shaped anti-rotation member 186 adapted to the guide wire exit opening. Again, this U-shaped member should match the same shape as the U-shaped lumen 190 formed on the inner member. With both the inner and outer member retaining the same U-shaped configuration, the two members will align together and slide axial to each other without independent rotation. The axial movement between the inner and outer members at the guide wire junction should not affect the positioning of the guide wire 202 within the guide wire exit notch since the inner and outer member will not rotate to misalign the respective notches formed therein. It should be appreciated to those skilled in the art that other methods for forming the U-shape on the anti-rotation member can be implemented without departing from the spirit and the scope of the present invention. Also, as mentioned above, the anti-rotation member and the lumen of the inner member can be formed in shapes other than a U-shape.
Referring now to
Referring now to
The purpose of the funnel introducer 216 in conjunction with the hemostatic valve 214 is to relieve the pressure which may be exerted on the outer member 218 and guide wire 220. As is shown in
The stent as described herein can be formed from any number of materials, including metals, metal alloys and polymeric materials. Preferably, the stent may be formed from metal alloys such as stainless steel, tantalum, or the so-called heat sensitive metal alloys such as nickel titanium (NiTi). Stents formed from stainless steel or similar alloys typically are designed, such as in a helical coil or the like, so that they are spring biased outwardly.
With respect to all of the embodiments disclosed above, some of the components of inner member and outer member can be formed from stainless steel or nickel-titanium hypotube, as noted above, or polymeric materials including polyethylenes, polyethylterpthalates, nylons, polyurethanes, elastomeric polyesters and the like. Generally speaking, the more proximal portions of inner member and outer member can be formed from material that is stiffer than the distal section so that the proximal section has sufficient pushability to advance through the patient's vascular system. On the other hand, the more distal portion of inner member and outer member can be formed of a more flexible material so that the distal portion of the catheter will remain flexible and track more easily over the guide wire.
The distal portion of the outer member which forms the restraining sheath portion of any of the embodiments of the self-expanding stent delivery system can be made with a Nylon-coated polyimide material that provides high-strength tubing, with a low-wall thickness. Such a material can resist an equal amount of hoop stress at a much lower wall thickness than with a Nylon material alone. In one component, a nylon material is bonded to the outside of a polyimide tubing. The inner surface of the polyimide tubing remains resistant to stent-strut indentation caused by the outward radial force exerted by the collapsed self-expanding stent. The Nylon material bonded to the outside of the sheath provides the necessary tubing strength to restrain the stent in a collapsed delivery position, but with a lower wall thickness. As a result, the profile of the stent delivery system can be reduced at its distal region by utilizing such a composite material.
Other modifications and improvements may be made without departing from the scope of the invention. For example, the leaf spring is not limited to the shape exemplified in the drawings, but may be any expanding member and may assume any shape which expands to protrude through an opening or slot in the outer member. Accordingly, it is not intended that the invention be limited, except as by the appended claims.
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|International Classification||A61L29/00, A61M25/00, A61F2/84, A61F2/06|
|Cooperative Classification||A61F2/95, A61M2025/0183, A61F2/966|
|European Classification||A61F2/966, A61F2/95|
|27 Apr 2004||AS||Assignment|
Owner name: ADVANCED CARDIOVASCULAR SYSTEMS, INC., CALIFORNIA
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:GEISER, TIMOTHY A.;PETERSON, CHARLES A.;DENISON, ANDY;AND OTHERS;REEL/FRAME:015264/0256;SIGNING DATES FROM 20040310 TO 20040415
Owner name: ADVANCED CARDIOVASCULAR SYSTEMS, INC., CALIFORNIA
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:GEISER, TIMOTHY A.;PETERSON, CHARLES A.;DENISON, ANDY;AND OTHERS;SIGNING DATES FROM 20040310 TO 20040415;REEL/FRAME:015264/0256
|24 Jun 2014||FPAY||Fee payment|
Year of fee payment: 4